Blood flow meter apparatus and method of use

ABSTRACT

A strobed blood flow meter provides periodic measurements of blood flow velocity or volumetric blood flow over a cardiac cycle at reduced average power consumption, which is advantageous for reducing battery size, and extending device battery life, such as in an implantable application. Continuous wave Doppler, pulsed Doppler, laser Doppler, transit time, electromagnetic flow, and thermal dilution techniques are included. Strobing provides higher level excitation during active periods, which improves signal-to-noise ratio, and provides a low power standby mode during an idle time between active periods. The invention may be used for chronic or acute applications. Doppler or other signals may be telemetered from an implanted portion of the flow meter for further signal processing to extract velocity or volumetric flow. Alternatively, such signal processing is also implanted, such that the velocity signal can be telemetered to an remote monitor.

CROSS REFERENCE TO RELATED APPLICATION(S)

This application is a division of U.S. patent application Ser. No.09/452,332, filed on Nov. 30, 1999, which in turn is a continuation ofU.S. patent application Ser. No. 09/179,042, filed on Oct. 26, 1998, nowU.S. Pat. No. 6,063,034, which is a division of U.S. patent applicationSer. No. 08/744,360, filed on Nov. 7, 1996, now U.S. Pat. No. 5,865,749,the specifications of which are incorporated herein by reference.

FIELD OF THE INVENTION

This invention relates to estimation of fluid flow, and moreparticularly to a chronic or acute measurement of blood flow in a bloodvessel.

BACKGROUND

There are many applications in clinical and research medicine in whichmeasurement or estimation of volumetric blood flow within a blood vesselis desirable. One method of making such measurements uses ultrasonicDoppler techniques to measure blood flow velocity and thereby estimatevolumetric blood flow. Velocity of an object is often measured using theDoppler effect Single frequency ultrasonic energy is transmitted into anarea of tissue containing the blood flow to be measured. Thisinsonification of the area is typically referred to as illuminationResulting ultrasonic energy is reflected, or backscattered, from theilluminated area. Energy reflected from moving targets, such as fluidand blood cells, will be shifted in frequency from the illuminatingfrequency according to the well-known Doppler effect The Doppler shiftedfrequency provides a measure of the blood flow velocity.

In clinical and research applications, it is often necessary to studyblood flow for an extended period of time. Thus, in ambulatory livingorganisms, such as animal or human subjects, there is a need in the artto provide a battery-powered ultrasonic Doppler blood flow meter formeasuring blood flow velocity for an extended period of time, allowing ahuman or animal patient freedom of movement during the study andminimizing the need for supervision by the clinician. There is also aneed in the art to provide a small, low-power ultrasonic Doppler bloodflow meter that is suitable for implantation in a human or animalsubject. There is a further need in the art to provide an implantableultrasonic Doppler blood flow meter that maintains adequatesignal-to-noise (SNR) ratio for accurate velocity estimation.

SUMMARY

The present invention includes a method and apparatus for estimatingblood flow or blood flow velocity in a blood vessel over a period oftime. According to the method, at least part of the measurement circuitsused to estimate blood flow are automatically activated only during thetime an estimate is being obtained. At least part of the measurementcircuits are automatically deactivated during the time an estimate isnot being obtained These steps are performed repeatedly to provide asequence of blood flow estimates forming a blood flow waveformindicative of blood flow. More than one estimate is typically requiredto obtain a waveform representative of the blood flow.

The steps of activating and deactivating at least part of themeasurement circuits is repeatedly performed sufficiently frequently,either periodically or at irregular intervals, such that the blood flowwaveform substantially represents the variable blood flow. Power to atleast a portion of the measurement circuits is reduced or interruptedwhile the measurement circuits are deactivated.

Measurement of blood flow can be obtained through various blood flowmeasurement techniques, including: continuous wave (CW) Doppler flowmeasurement, pulsed Doppler flow measurement, laser Doppler flowmeasurement, transit time flow measurement, thermal dilution flowmeasurement, electromagnetic flow measurement, or other suitable flowmeasurement technique.

In several embodiments, a basebanded Doppler-shifted signal provides theblood flow estimate. In other embodiments, a blood flow output signal isderived from the basebanded Doppler-shifted signal and provided as theblood flow estimate.

Thus, the present invention provides a strobed blood flow meter, such asan implantable strobed ultrasonic Doppler blood flow meter, havingreduced average power consumption, which is advantageous for reducingbattery size, extending battery life, and improving signal-to-noiseratio.

BRIEF DESCRIPTION OF THE DRAWINGS

In the drawings, like numerals describe substantially similar componentsthroughout the several views.

FIG. 1 is a block diagram of one embodiment of the invention.

FIG. 2 is a block diagram illustrating one embodiment of the mixer ofFIG. 1 in more detail.

FIG. 3 is a block diagram illustrating one embodiment of the transducerof FIG. 1 in more detail

FIG. 4 is a block diagram illustrating one embodiment of the controlcircuit of FIG. 1 in more detail.

FIG. 5A is a graph illustrating generally voltage vs. time waveforms forone embodiment in which the invention is operated.

FIG. 5B is a graph illustrating generally a velocity vs. time signal inoperation of the embodiment of FIG. 5A, but on a compressed time scalewith respect to the illustration of FIG. 5A

FIG. 6 is a block diagram illustrating one embodiment of the presentinvention in which certain components are turned off during the idleperiod.

FIG. 7 is a block diagram illustrating another embodiment of the presentinvention in which certain components are turned off during the idleperiod.

FIG. 8 is a block diagram illustrating a further embodiment of thepresent invention in which certain components are turned off during theidle period.

FIG. 9 is a block diagram illustrating in more detail the controlcircuit of FIG. 8 in more detail.

FIG. 10 is a block diagram illustrating an embodiment of the presentinvention including an impedance matching network.

FIG. 11 is a block diagram illustrating an embodiment of the presentinvention including a signal processor.

FIG. 12 is a block diagram illustrating one embodiment of the signalprocessor of FIG. 11 in more detail.

FIG. 13 is a graph generally comparing the strobed continuous wave andpulse Doppler ultrasonic frequency waveforms.

FIG. 14 is a block diagram illustrating one embodiment of the presentinvention using transit time techniques of blood flow velocityestimation.

FIG. 15 is an end view of the embodiment illustrated in FIG. 14.

DETAILED DESCRIPTION

In the following detailed description, reference is made to theaccompanying drawings which form a part hereof, and in which is shown byway of illustration specific embodiments in which the invention may bepracticed. These embodiments are described in sufficient detail toenable those skilled in the art to practice the invention, and it is tobe understood that the embodiments may be combined, or that otherembodiments may be utilize and that structural, logical and electricalchanges may be made without departing from the spirit and scope of thepresent invention. The following detailed description is, therefore, notto be taken in a limiting sense, and the scope of the present inventionis defined by the appended claims and their equivalents.

The present invention provides a strobed blood flow meter useful forchronic or acute estimates of blood flow or blood flow velocity andhaving reduced average power consumption, which has advantages thatinclude reducing battery size and extending battery life. As discussedand defined herein, estimating volumetric blood flow and blood flowvelocity are understood as interchangeable concepts, since estimates ofvolumetric blood flow are obtained from estimates of blood flow velocityby multiplying blood flow velocity with a known constant cross-sectionalarea of a blood vessel. When the cross-sectional area of the bloodvessel is unknown, a signal proportional to estimates of blood flow canstill be provided from estimates of blood flow velocity since thecross-sectional area of the blood vessel is assumed to be relativelyconstant.

As used herein, the term “strobing” is defined as repeatedly estimatingblood flow velocity during a period of interest, as discussed below. Ina living organism having a circulatory system with a cardiac cycle,which is defined as the period between successive heartbeats, the periodof interest for strobing may be one or more such cardiac cycles.However, it is also desirable to repeatedly estimate blood flow velocityover a period of interest when no cardiac cycle is present. For example,certain embodiments of an artificial heart pump may be implementedwithout the periodic pulsing associated with a heartbeat. In suchsystems, it may still be desirable to repeatedly estimate blood flowvelocity over some other period of interest.

As will be described in detail below, the present invention encompassesstrobing or automatically activating certain portions of the blood flowmeter during an active period in order to obtain an ultrasonic Dopplerblood flow velocity estimate, and later automatically deactivating theseportions of the blood flow meter during an idle time between suchestates. As a result, average power consumption is advantageouslyreduced. Strobing according to the present invention includes a widevariety of blood flow measurement techniques, including, but not limitedto: ultrasonic Doppler blood flow measurement, such as both continuouswave (CW) and pulsed Doppler blood flow measurements; transit timemeasurements; electromagnetic flow measurements; thermal dilutionmeasurements; and laser Doppler measurements, each of which is describedfurther below.

FIG. 1 is a block diagram illustrating one embodiment of the presentinvention. In FIG. 1, strobed ultrasonic blood flow meter 100 is capableof being implanted in a human or animal subject for measurement of bloodflow in blood vessel 105. Blood flow meter 100 comprises oscillator 110,which is a sine or square wave oscillator operating at a carrierfrequency in an ultrasonic region of the frequency spectrum, typicallyin the 5-20 MHz range, though other frequencies are also possible. Theultrasonic sine or square wave output signal of oscillator 110 at node115 is referred to as a carrier signal. The carrier signal frequency atnode 115 is in the ultrasonic frequency range, and is electricallycoupled to a control circuit 120 at control circuit oscillator input125. Control circuit 120 produces at control circuit output 130 aresulting electrical strobed ultrasonic-frequency signal (shown assignal 145V in FIG. 5A) which is electrically coupled to amplifier input135 of power amplifier 140 through node 145. In response, amplifier 140produces a resulting electrical strobed amplified ultrasonic-frequencysignal at amplifier output 150, which is electrically coupled throughnode 165 to transducer electrical input 155 of transducer 160. Inresponse, transducer 160 provides, at transducer ultrasound output 170,ultrasonic energy that is mechanically or acoustically coupled to tissueincluding blood vessel 105. In this patent application, providingultrasonic energy, insonifying, and insonating, are all referred togenerally as illuminating.

Illumination of blood vessel 105 results in a reflected Doppler-shiftedultrasound signal, also referred to as a backscattered signal, that isreceived at transducer ultrasound input 175, and converted by transducer160 into a Doppler-shifted electrical signal at transducer electricaloutput 180. The Doppler-shifted electrical signal is electricallycoupled through node 195 to receiver input 185 of receiver 190, whichprovides a buffered Doppler-shifted signal in response thereto atreceiver output 200.

Mixer 205 receives the buffered Doppler-shifted signal at mixer input210 through node 215. Mixer 205 also receives through node 115 thecarrier signal of oscillator 110 at mixer oscillator input 220. Mixer205 performs a demodulation function by quadrature mixing, as describedbelow, producing an in-phase (I) signal at in-phase (I) output 225 and aphase-shifted (Q) signal, which is 90 degrees out of phase with respectto the I signal, at phase-shifted (Q) output 230. The I and Q signalseach have components that include difference and sum frequencycomponents that are approximately equal to the respective difference andsum of the frequencies of the carrier signal and the bufferedDoppler-shifted signal. The I and Q signals may also contain a carrierfrequency component, also referred to as carrier feedthrough.

The I signal is electrically coupled through node 235 to a first lowpass filter input 240 of first low pass filter 245. First low passfilter 245 removes the carrier feedthrough and the sum frequencycomponents of the I signal, and provides the difference frequencycomponent at the first low pass filter output 250. The differencefrequency component at the first low pass filter output 250 is referredto as the basebanded in-phase Doppler signal or the basebanded I Dopplersignal. Similarly, the Q signal is electrically coupled through node 255to a second low pass filter input 260 of second low pass filter 265.Second low pass filter 265 removes the carrier feedthrough and the sumfrequency components of the Q signal and provides the differencefrequency component at the second low pass filter output 270. Thedifference frequency component at the second low pass filter output 250is referred to as the basebanded phase-shifted Doppler signal, or thebasebanded Q Doppler signal.

The basebanded I and Q Doppler signals are electrically coupled throughrespective nodes 275 and 280 to respective inputs of telemetry circuit285. In one embodiment, the basebanded I and Q Doppler signals areremodulated with a telemetry carrier frequency for transmission to aremote telemetry device 282, such as an external telemetry receiver. Inanother embodiment, as described below, an analog velocity output signalis produced, which is encoded, such as by pulse position modulation, fortransmission to remote telemetry device 282. Thus, telemetry circuit 285allows transmission of the signals corresponding to the basebanded I andQ Doppler signals from implanted blood flow meter 100 to a remotetelemetry device 282 for further precessing. In one embodiment, thisfurther processing includes velocity determination according to thewell-known Doppler equation, illustrated in Equation (1).$\begin{matrix}{v = \frac{f_{d}C}{2f_{c}\cos \quad \theta}} & (1)\end{matrix}$

In Equation (1): v is the blood flow velocity to be determined; f_(d) isthe (basebanded) received Doppler shifted frequency reflected from theblood flow, C is the speed of sound in the medium, e.g. tissue; f_(c) isthe carrier frequency; and θ is the angle formed by the velocity vectorof the blood flow and the path along which the illuminating ultrasonicenergy is provided.

FIG. 2 is a block diagram illustrating one embodiment of mixer 205 inmore detail. In FIG. 2, mixer 205 includes quadrature phase splitter300, first multiplier 305, and second multiplier 310. Splitter 300receives, through node 115, the carrier signal at splitter input 315,and produces in response thereto a resulting in-phase carrier signal atnode 320 and a phase-shifted carrier signal at node 325 that isphase-shifted by 90 degrees with respect to the in-phase carrier signal.The in-phase carrier signal at node 320 and the phase-shifted carriersignal at node 325 are substantially quadruture balanced, i.e. they aresubstantially matched in amplitude, and have a phase difference which isvery close to 90 degrees. The buffered Doppler signal at node 215 ismultiplied at first multiplier 305 by the in-phase carrier signal atnode 320 to produce the I signal at node 235. The buffered Dopplersignal at node 215 is also multiplied at second multiplier 310 by thephase shifted carrier signal at node 325 to produce the Q signal at node255.

FIG. 3 is a block diagram illustrating one embodiment of transducer 160in more detail, in relation to blood vessel 105. In FIG. 3, transducer160 includes ultrasound transmit transducer 330 and ultrasound receivetransducer 335. Transmit and receiver transducers 330 and 335 arepreferably single piston piezoelectric transducers, comprised ofmaterials such as lead zirconate titanate (PZT) crystal or compositematerials. Other piezoelectric crystal, ceramic, or polymer, or anyother suitable transducer may also be used.

Transmit transducer 330 receives the electrical strobed amplifiedultrasonic-frequency signal at input 155 and provides, or launches,continuous wave (CW) ultrasonic energy at transducer ultrasound output170 for illumination of blood vessel 105. Illumination of blood vessel105 results in a reflected Doppler-shifted ultrasound signal attransducer ultrasound input 175 that is received by receive transducer335 and converted into an electrical received Doppler-shifted signal attransducer electrical output 180. In FIG. 3, separate transmit andreceive transducers 330 and 335 are used for simultaneously illuminatingand receiving CW Doppler ultrasound. However, it is understood that asingle transducer could also be used for sequentially illuminating andreceiving pulsed Doppler ultrasound, as described below.

FIG. 4 is a block diagram illustrating one embodiment of control circuit120 in more detail. In FIG. 4, control circuit 120 includes sine wave tosquare wave converter 350, digital control logic 355, and strobingswitch 360. Converter 350 receives the carrier signal at node 115 andprovides to digital control logic 355 a square wave clock signal at node365, which can be divided down to lower frequencies if desire. Converter350 is omitted if oscillator 110 is a square wave, rather than a sinewave oscillator. Logic 355 provides a periodic strobing control signalat node 370, also available at strobing control signal output 371, tocontrol the conductance of the carrier signal at node 115 throughstrobing twitch 360 to control circuit output 130. However, the periodicstrobing control signal at node 370 could alternatively be provided atirregular intervals. A resulting electrical strobed ultrasonic-frequencysignal is provided through node 145 for amplification by amplifier 140and conversion into ultrasound energy by transducer 160.

FIG. 5A is a voltage vs. time graph illustrating generally timing in oneembodiment in which the present invention is operated. FIG. 5A includesstrobing control signal 370V at node 370 and the strobed ultrasonicfrequency signal 145V at node 145. A corresponding velocity vs. timegraph is illustrated in FIG. 5B, but with time illustrated on acompressed time scale with respect to that in FIG. 5A. In FIG. 5A,strobing control signal 370 is a periodic control signal having acorresponding strobing period, t_(strobe). The strobing period iscomprised of an active period, t_(on), and an idle period, t_(off).

During the active period of the strobing control signal 370V, thecarrier frequency signal at node 115 is conducted to node 145 throughthe strobing switch 360, as illustrated during the corresponding portionof the strobed ultrasonic frequency signal 145V. During the idle periodof the strobing control signal 370V, the carrier frequency signal atnode 115 is isolated from node 145 by the strobing switch 360, asillustrated during the corresponding portion of the strobed ultrasonicfrequency signal 145V. Blood vessel 105 is illuminated during eachactive period of the strobing control signal 370V, as illustrated inFIG. 5A. Velocity is determined near the end of each active period ofthe strobing control signal 370V, such as at times t₁, t₂, and t₃, asillustrated in FIGS. 5A and 5B.

Blood velocity will vary depending on the size and physiologicallocation of the blood vessel 105 being measured. Blood velocity willalso vary as a function of time during the cardiac cycle, i.e. duringand between successive heartbeats. One embodiment of the presentinvention uses a programmably adjustable strobing frequency, which isthe inverse of the strobing period. The strobing frequency should behigh enough to provide a representative estimated velocity vs. timewaveform both during the cardiac cycle and over many cardiac cycles. Forexample, in most larger mammals, heart rate varies from between 40 to200 beats per minute. A strobing frequency of 50 Hz respectivelyprovides 75 and 15 estimated velocity data points for each of theserespective heart rates. For smaller mammals, such as rats, heart ratemay approach 400 beats per minute. Increasing strobing frequency to 100Hz would still allow 15 estimated velocity data points for this case.

The particular strobing frequency may be selected to obtain the desiredtime resolution of velocity estimates. The desired time resolution ofvelocity estimates may in turn be selected to accommodate the expectedrate of change of blood flow velocity in the blood vessel. The rate ofchange of the blood flow velocity is typically higher for an arterialblood vessel 105 that is more proximal to the heart than for an arterialblood vessel 105 that is more distal from the heart or for a venal bloodvessel 105. As set forth above, t_(strobe) will exceed t_(on). But themaximum value of t_(strobe) will depend on many factors, includingwhether an accurate reconstruction of the velocity waveform is needed orwhether the velocity estimates are used only to determine blood flow,such that fewer estimates per cardiac cycle may suffice.

In one embodiment, active period, t_(on), is minimized to minimizeaverage power consumption or to obtain other advantages, as describedbelow. However, the minimum active period is typically longer than somecombination of: a system bandwidth; a stabilization time; and amean-frequency estimation time.

The system bandwidth is defined as the inverse of the maximum expectedbasebanded I and Q Doppler signal frequencies, which can be calculatedfrom the well-known Doppler equation for a particular blood velocity.

The stabilization time is the time required to power up and stabilizecertain electronic circuits which are powered down during the idleperiod. The required stabilization time may be dominated by, forexample, the filter time-constants of first and second low pass filters245 and 265, if these filters were powered down during the idle period.In another example, the required stabilization time may be dominated bythe charging of a power supply output capacitor from which power issupplied to those electronic circuits that were turned off during theidle period. Separate control signals may be provided to individualelectronic circuits to tailor the time that the circuits are powered tomeet their individual stabilization requirements. For example, first andsecond low pass filters 245 and 265 may be turned on prior to providingthe electrical signal to drive transducer 160 to accommodate longerstabilization time requirements of first and second low pass filters 245and 265.

The mean frequency estimation time is determined by the number ofsamples of the basebanded I or Q Doppler signals at respective nodes 275and 280 that must be acquired to accurately estimate the blood velocityfor a particular velocity estimate. The mean frequency estimation timedepends, in turn, on the particular mean frequency estimation techniqueused. In one embodiment, sophisticated digital signal processingtechniques are used to extract a relatively accurate mean frequencyestimate from as few as 8 of the samples. In another embodiment,zero-cross detection techniques are used to provide a root mean square(rms) reading of mean frequency from more than 100 samples.

The present invention uses strobed ultrasonic energy, whichadvantageously reduces its average power consumption. This isparticularly important when power is drawn from a fixed resource, suchas a battery, which is implanted in vivo together with the electronicsof blood flow meter 100 and cannot be easily replaced. In suchsituations, the reduced average power consumption of the presentinvention is critical for extending battery life of blood flow meter100. The average power consumption of the present invention isillustrated by Equation (2). $\begin{matrix}{{Power} = \frac{{P_{on}t_{on}} + {P_{off}t_{off}}}{t_{strobe}}} & (2)\end{matrix}$

In Equation (2), P_(on) is the power consumption during the activeperiod and P_(off) is the power consumption during the idle period. Asexplained below, most of the electronics of blood flow meter 100 arepowered on during the active period, but only a subset of theseelectronics are powered on during the idle period For this reason,P_(on) exceeds P_(off). Thus, as illustrated in Equation (2), averagepower consumption is minimized by: reducing the duration of the activeperiod; and, increasing the strobing period; and, decreasing both P_(on)and P_(off), particularly P_(on).

FIG. 6 is a block diagram illustrating one embodiment of the presentinvention in which only amplifier 140 and telemetry 285 are turned offduring the idle period. The strobing control signal at node 370 iselectrically coupled to switchably control the conductances between eachof amplifier 140 and telemetry 285 blocks and their respective powersupplies. Transducer 160 typically does not draw any bias current, butuse of any transducer that does draw bias current could similarly haveits bias current switchably controlled by strobing control signal 370.By leaving other blocks powered during the idle period, stabilizationtime is reduced, as described above. However, this embodiment does notminimize average power consumption as much as other possibleembodiments.

FIG. 7 is a block diagram illustrating another embodiment of the presentinvention in which amplifier 140, receiver 190, mixer 205, fist andsecond low pass filters 245 and 265, and telemetry 285 are all turnedoff during the idle period. The strobing control signal at node 370 iselectrically coupled to switchably control, either independently or ingroups, the conductances between each of amplifier 140, receiver 190,mixer 205, first and second low pass filters 245 and 265, and telemetry285 and their respective power supplies. Since more components arepowered down during the idle period, this embodiment decreases averagepower consumption further from that of FIG. 6, but stabilization timemay be increased, as explained above.

FIG. 8 is a block diagram illustrating another embodiment of the presentinvention in which oscillator 110, amplifier 140, receiver 190, mixer205, first and second low pass filters 245 and 265, and telemetry 285are all turned off during the idle period. The strobing control signalat node 370 is electrically coupled to switchably control, eitherindependently or in groups, the conductances between each of oscillator10, amplifier 140, receiver 190, mixer 205, first and second low passfilters 245 and 265, and telemetry 285 and their respective powersupplies. FIG. 8 uses a control circuit 400, which is illustrated inmore detail in FIG. 9. Since more components are powered down during theidle period, this embodiment decreases average power consumption furtherfrom that of FIGS. 6-7.

FIG. 9 is a block diagram illustrating in more detail the controlcircuit 400 of FIG. 8. In FIG. 9, a separate timing generator 410 isprovided for coupling a clock signal through node 365 to digital controllogic 355. As in the embodiments illustrated in FIGS. 1 and 6-7, atleast a portion of the digital control logic remains powered during theidle period in the embodiment illustrated in FIGS. 8-9. In theembodiment illustrated in FIGS. 8-9, the timing generator 410 alsoremains powered during the idle period. Timing generator 410 is capableof being operated at a lower frequency than the ultrasonic frequenciesof oscillator 110. Use of timing generator 410 allows the higherfrequency oscillator 110 to be powered down during the idle period. Thisresults in further average power savings in some implementations of thepresent invention.

Thus, the invention described above in FIGS. 1-9 provides a method ofestimating the velocity of blood flow in a blood vessel. At least partof the measurement circuits are automatically activated only during thetime an estimate is being obtained. At least part of the measurementcircuits are deactivated during the time an estimate is not beingobtained. These steps are performed repeatedly to provide a sequence ofblood flow estimates forming a blood flow waveform indicative of bloodflow. More than one estimate is required to obtain the blood flowwaveform.

According to one embodiment of the present invention, ultrasonic energyis repeatedly applied to the blood flow in the blood vessel, eitherperiodically or at irregular time intervals over a period of time, suchas during all or a portion of one or more cardiac cycles. A portion ofthe applied energy is reflected from the blood flow to produce areflected ultrasonic energy signal. The reflected ultrasonic energy isreceived for further processing from which blood flow velocity ismeasured. Electronic circuits are powered off or down between therepeated applications of ultrasonic energy, thereby allowing increasedlevels of illumination while maintaining or reducing average powerconsumption.

As described above, one embodiment of the present invention uses strobedultrasonic energy, which advantageously reduces its average powerconsumption because portions of the present invention are powered offbetween strobing instances. This advantage, or a portion thereof, may betraded for improved signal-to-noise ratio (SNR), which is also adesirable characteristic for accurate measurement of blood flowvelocity. For example, transducer 160 is capable of providing higherlevel illumination of blood vessel 105 than in a conventional system,because strobed ultrasonic energy is used, i.e. the higher levelillumination is limited to a shorter duration. Since blood vessel 105 isilluminated at a higher level, more reflected energy is available fordetection, thereby improving the SNR.

Similar signal processing improvements are also available, for example,by using higher supply currents for shorter durations in those otherblocks that are capable of being powered down during the idle period,such as receiver 190, mixer 205, and first and second low pass filters245 and 265. These signal processing improvements obtained from highercurrent levels for shorter durations include better noise performanceand higher bandwidth These improvements provided by the presentinvention are particularly advantageous for the receiver 190 and mixer205 blocks, which require bandwidths capable of accommodating aDoppler-shifted signal centered around the 5-20 MHz carrier frequency.Thus, the strobed ultrasonic blood flow velocity measurements of thepresent invention offer considerable advantages in addition to reducedaverage power consumption.

Trading off the average power savings of the strobed CW Doppler systemof present invention for higher power during the active period isfurther illustrated by way Example 1, comparing the present invention toa conventional CW Doppler system

EXAMPLE 1

Conventional CW Doppler Strobed CW Doppler I_(avg) = 2mA I_(avg) = 2mAt_(strobe) = 20 ms (50 Hz strobing) t_(on) = 2 ms t_(off) = 18 msI_(idle) = 500 μA during t_(off) I_(active) = 15.5 mA during t_(on)

Example 1 illustrates, for a 50 Hz strobing frequency and(t_(on)/t_(strobe))=10%, the strobed current can be as high as 15.5 mAfor an idle current of 500 μA. Thus, in this example, the current can beelevated by a factor of 7.75 in the strobed CW Doppler system withoutincreasing the average power consumption over a conventional CW Dopplersystem.

FIG. 10 is a block diagram illustrating another embodiment of thepresent invention in which an impedance matching network 450 has beeninterposed between amplifier output 150 and transducer electrical input155. Network 450 includes passive impedance matching components tomaximize power transfer between amplifier 140 and transducer 160 at thecarrier frequency, where amplifier 140 typically presents an impedancethat is unmatched to that of transducer 160.

The impedance matching network results in more efficient power transferat the output of network 450 at node 165B for the strobed CW Dopplersystem of the present invention over a conventional CW Doppler system,as illustrated in Example 2.

EXAMPLE 2

Conventional CW Doppler Strobed CW Doppler Z_(out) = 2000Ω at carrierfrequency Z_(out) = 400Ω at carrier frequency Z_(tran) = 20Ω at carrierfrequency Z_(tran) = 20Ω at carrier frequency Z_(network) = 100 to 1matching Z_(network) = 20 to 1 matching I_(amp) = 1 mA peak I_(amp) = 5mA peak during active period V_(amp) = 4V_(p-p) continuous V_(amp) = 4V_(p-p) during active period P_(amp) = 1 mW P_(amp) = 10 mWP_(transducer) = 1 mW P_(transducer) = 10 mW V_(transducer) = 0.25V_(p-p) V_(transducer) = 0.89 V_(p-p)

In Example 2: Z_(out) is the output impedance of amplifier 140 atamplifier output 150 at the ultrasonic carrier frequency; Z_(tran) isthe impedance of transducer 160 at the carrier frequency; Z_(network) isthe impedance matching ratio of network 450; I_(amp) is the peak outputcurrent of amplifier 140; V_(amp) is the peak-to-peak output voltage ofamplifier 140; P_(amp) is the power output of amplifier 140;P_(transducer) is the power input of transducer 160; and, V_(transducer)is the peak-to-peak input voltage of transducer 160.

In Example 2, the conventional CW Doppler system is operatedcontinuously, and the strobed CW Doppler system is operated at a 10%duty cycle (t_(on)/t_(strobe)) with the negligible current during theidle period. As seen in Example 2, amplifier 140 and network 450 of thestrobed Doppler system of FIG. 10 allow higher power output fromamplifier 140, and a higher input voltage of transducer 160. Thisproduces a higher level illumination, resulting in more reflectedultrasonic energy, and thereby improving the SNR.

FIGS. 1-10 illustrate various embodiments of the present invention inwhich the basebanded I and Q Doppler signals are telemetered to othercircuits for further processing to determine the blood flow velocityestimate. In one embodiment, for example, the basebanded I and Q Dopplersignals are telemetered from an implanted portion of the blood flowmeter 100 to accompanying external circuits for further processing.However, signal processing of the basebanded I and Q Doppler signals canalso be carried out within the implanted blood flow meter 100.

FIG. 11 is a block diagram illustrating an embodiment of the presentinvention in which a signal processor 470 is contained within theimplanted blood flow meter 100. In FIG. 11, signal processor 470receives the basebanded I and Q Doppler signals at respective nodes 275and 280, and produces a blood flow output signal or velocity outputsignal representing the estimated blood flow velocity. The velocityoutput signal is electrically coupled through node 475 to telemetry 285,where it is transmitted from the implanted blood flow meter 100 to anexternal receiver.

FIG. 12 is a block diagram illustrating one embodiment of signalprocessor 470 that is particularly useful in applications having asingle-ended power supply, such as a battery in the implantable bloodflow meter 100 of the present invention. In FIG. 12, signal processor470 contains a voltage reference 500, which provides a stable outputbias voltage at node 505 to a first input of each of first and secondamplifiers 510 and 520 and first and second zero cross detectors 530 and540. First and second amplifiers 510 and 520 provide gain, or provideboth gain and level-shifting. First and second amplifiers may also beused to provide bandpass filtering. A second input of first amplifier510 receives the basebanded I Doppler signal at node 275. A second inputof second amplifier 520 receives the basebanded Q Doppler signal at node280.

First amplifier 510 provides a buffered basebanded I Doppler signal atnode 545 to a second input of first zero cross detector 530. Secondamplifier 520 provides a buffered basebanded Q Doppler signal at node550 to a second input of second zero cross detector 540. First andsecond zero cross detectors 530 and 540 provide first and second zerocross outputs at respective nodes 555 and 560. The first and second zerocross outputs at respective nodes 555 and 560 each change logic state inresponse to the voltage of respective buffered I and Q Doppler signalspassing through the bias voltage at node 505. Each of the resultingpulsatile voltages waveforms at the first and second zero cross outputsis approximately 90 degrees out of phase with the other, and is at thebasebanded Doppler frequency.

Quadrature encoder 565 receives the first and second zero cross outputsat respective nodes 555 and 560. The 90 degree phase difference betweenthe voltage waveforms at nodes 555 and 560 make it possible to determinetheir phase relationship at each logic voltage transition of thesevoltage waveforms at nodes 555 and 560. Quadrature encoder 565 containslogic circuitry for determining the phase relationship between the firstand second zero cross outputs at nodes 555 and 560, and does so at eachvoltage transition at each of nodes 555 and 560. In response to eachsuch determination, quadrature encoder 565 provides a fixed-durationvoltage pulse to only one of forward node 570 or reverse node 575.

Differential frequency-to-voltage converter 580 receives voltage pulsesat each of the respective forward and reverse nodes 570 and 575, andprovides a resulting blood flow output signal such as the analogvelocity output signal at node 475. In one embodiment, converter 580provides charge integration of the fixed-duration voltage pulses at eachof the respective forward and reverse nodes 570 and 575, and providesthe resulting blood flow output signal in response thereto. The chargeof the voltage pulses at the forward node 570 incrementally increasesthe velocity output signal at node 475, and the charge of the voltagepulses at the reverse node 575 incrementally decreases the velocityoutput signal at node 475. Converter 580 could also be implemented as anup-down counter providing an output count representative of the velocityoutput signal. Voltage pulses received at forward node 570 increment theoutput count, and voltage pulses received at reverse node 575 decrementthe output count, or vice versa.

Thus, signal processor 470 is capable of providing, using a single-endedpower supply, an analog velocity output signal at node 475 containingboth magnitude and directional information of blood flow velocity. Theanalog velocity output signal at node 475 can be repeatedly sampled toprovide a sequence of blood flow estimates forming a blood flow waveformindicative of blood flow. The analog velocity output signal at node 475or the samples derived therefrom can be further processed andtransmitted from the implanted blood flow meter 100.

FIGS. 1-12 illustrate various bidirectional embodiments of the presentinvention that are capable of determining the magnitude and direction ofblood flow velocity. If direction information is not needed, aunidirectional embodiment of the present invention could be used. In aunidirectional embodiment of the present invention, one of the I or Qchannels is omitted. In mixer 205, a quadrature phase splitter 300 isomitted and only one of first and second multipliers 305 and 310 isneeded. In signal processor 470, quadrature encoder 565 is replaced by amonostable oscillator (one-shot) providing a fixed-duration pulse, anddifferential frequency-to-voltage converter 580 is replaced by asingle-ended frequency-to-voltage converter.

The present invention has been described above with respect to aparticular embodiment of strobed ultrasonic Doppler blood flow meter,i.e. a strobed continuous wave (CW) ultrasonic Doppler blood flow meter,referred to as a strobed CW Doppler blood flow meter. However, it isunderstood that the present invention is also broadly applicable to anyembodiment of a strobed ultrasonic Doppler blood flow meter and itsmethod of use.

For example, the invention encompasses the use of a strobed ultrasonicpulsed Doppler blood flow meter, referred to as a strobed pulsed Dopplerblood flow meter. The strobed pulsed Doppler embodiment alsoperiodically illuminates a blood vessel by a transducer, but eachillumination comprises bursts of pulsatile (or pulse train)ultrasonic-frequency energy. Each burst of ultrasonic-frequency energyfrom a particular illumination is reflected, or backscattered, from theblood flow and typically subsequently detected at the same transducer.Samples of the resulting electrical signal, each corresponding to aburst of pulsatile ultrasonic-frequency energy, are used to estimatemean frequency. A resulting blood flow velocity estimate is producedfrom the aggregation of mean frequency estimations within a particularstrobing.

FIG. 13 illustrates generally a comparison of the strobed ultrasonicfrequency signal waveforms used in each of the strobed CW and strobedpulsed Doppler embodiments. In FIG. 13, the strobing control signal 370Villustrates generally the active and idle periods in relation to thestrobing period. The CW embodiment provides an ultrasonic frequencysignal 145V continuously over the entire active period or at least someportion thereof. The strobed pulsed Doppler embodiment provides a pulsedultrasonic frequency signal 600 that typically contains more than oneburst of pulsatile ultrasonic-frequency energy over the active period orat least some portion thereof.

In fact, as illustrated in FIG. 13, the type of ultrasonic energy signalused is not essential to the invention. Thus, both of theabove-described ultrasonic blood flow meters have characteristics thatinclude: repeatedly illuminating the blood vessel with ultrasonic energyduring a cardiac cycle; repeatedly receiving during the cardiac cycle anultrasonic energy signal, which contains Doppler-shifted frequenciescorresponding to a blood flow velocity estimate, reflected from theblood flow; and, processing the received ultrasonic energy signal toobtain the blood flow velocity estimate from the Doppler-shiftedfrequencies contained therein.

In both species of strobed ultrasonic blood flow meters, the ultrasonicenergy is strobed repeatedly throughout the cardiac cycle or otherperiod of interest, with a strobing frequency which is substantiallylower than the ultrasonic energy frequency. In one embodiment of thepresent invention, each strobing instance corresponds to a resultingblood flow velocity estimate.

The above-described embodiments describe a blood flow meter thatestimates blood flow velocity by strobed Doppler measurements ofbackscattered ultrasonic energy. However, the strobed blood flow meteraccording to the present invention also includes other techniques ofestimating blood flow velocity, including, but not limited to: transittime measurements, electromagnetic flow measurements, thermal dilutionmeasurements, and laser Doppler measurements, each of which is describedfurther below.

FIG. 14 is a generalized schematic illustration of one embodiment of atransit time measurement of blood flow velocity that is encompassed bythe present invention. First and second transducers 650 and 655,respectively, are configured for ultrasonic communication therebetweenvia an acoustic reflector 660. A first ultrasonic impulse 665 islaunched from first transducer 650, reflected from reflector 660, andreceived at second transducer 655. A second ultrasonic impulse 670 islaunched from second transducer 655, reflected from reflector 660, andreceived at first transducer 650.

FIG. 14 illustrates the case where first impulse 665 has a directionalcomponent in the same direction as the blood flow in blood vessel 105,and second impulse 670 has a directional component opposite thedirection of blood flow in blood vessel 105. As a result, a travel timeof second impulse 670 from second transducer 655 to first transducer 650is longer than a travel time of first impulse 665 from first transducer650 to second transducer 655. Blood flow velocity is calculated from thedifference in transit times of the first and second impulses 665 and 670respectively.

In this embodiment, the invention includes a control circuit 675 forproviding a strobed ultrasonic frequency signal to each of respectivefirst and second amplifiers 680 and 685 through respective nodes 690 and695. Control circuit 675 optionally provides power control signals torespective first and second receivers 700 and 705 through respectivenodes 710 and 715. First and second amplifiers 680 and 685,respectively, provide an amplified strobed ultrasonic frequency signalat respective nodes 720 and 725 to respective first and secondtransducers 650 and 655, which provide the first and second impulses 665and 670 in response thereto.

First and second transducers 650 and 655 also receive respective secondand first impulses 670 and 665, as described above, and provideresulting electrical signals to respective first and second receivers700 and 705 through respective nodes 730 and 735. First and secondreceivers 700 and 705, respectively, provide buffered electrical signalsto processing circuit 740 through respective nodes 745 and 750.Processing circuit 740 calculates blood flow velocity from thedifference in transit times of the first and second impulses 665 and 670respectively, and provides through node 755 a signal containing bloodflow velocity information to telemetry device 760 for transmission to aremote telemetry device. Control circuit 675 optionally provides a powercontrol signal to processing circuit 740 through node 765 for reducingor removing power from processing circuit 740 between transit timeestimates of blood flow velocity. As described above, control circuit675 may also optionally provide a power control signal to telemetrydevice 760 to reduce or remove power from telemetry device 760 when itis not transmitting a transit time estimate of blood flow velocity.

FIG. 15 illustrates an end view of the configuration of FIG. 14. In FIG.15, first and second transducers 650 and 655, respectively, andreflector 660 are arranged such that first and second impulses 665 and670, respectively, each provide an insonification area 770 that includesthe entire area of blood vessel 105, such that an average estimate ofblood flow over the area of blood vessel 105 is provided. The transittime estimate of blood flow velocity may also be improved by averagingmultiple transit time measurements to provide a single estimate of bloodflow velocity. In such an embodiment, control circuit 675 reduces orremoves power from other circuits between each series of transit timemeasurements used to provide a blood flow velocity estimate. A sequenceof blood flow estimates forms a waveform representative of blood flowover a period of time.

The present invention also includes the use of electromagnetic flowtechniques to estimate blood flow velocity. In one embodiment of thistechnique, first and second electrodes are disposed across an interposedblood vessel such that the blood flow is in a direction that issubstantially orthogonal to a vector between the first and secondelectrodes. A permanent magnet or electromagnet is used to create amagnetic field through the blood vessel in a direction that issubstantially orthogonal to both the direction of blood flow and thevector between the first and second electrodes. As a result, ionizedparticles within the blood flow are deflected toward one of the firstand second electrodes, resulting in a voltage difference therebetweenthat is proportional to the blood flow velocity. The invention uses theabove-described strobing technique to reduce or remove power betweenblood flow estimates to circuits within the blood flow meter, such as tothe electromagnet, if any, or to sensing and processing circuits thatdetect the voltage difference between the first and second electrodes,or to telemetry circuits that transmit electromagnetic flow estimates ofblood flow velocity to a remote telemetry device.

The present invention also includes the use of thermal dilutiontechniques to estimate blood flow. In one embodiment of this technique,a heater is used to pulsedly heat the blood, and the heated blood pulseis detected by a temperature sensor located at a known distance from thepoint of heating in the direction of the blood flow. Volumetric bloodflow is calculated from the time between the heating of the blood pulseand the detection of the blood pulse. Several heated blood pulses aretypically introduced and detected to produce a more accurate blood flowestimate.

In another embodiment of this technique, a single thermistor is used forboth heating and detection. A heated thermistor is introduced into theblood vessel such that it is in thermal contact with the blood flow, andcooling of the thermistor is effected by the blood flow. Blood flow at ahigher velocity cools the thermistor at a higher rate than blood flow ata lower velocity. The energy delivered to the thermistor to maintain thethermistor at a constant temperature is proportional to blood flowvelocity. Alternatively, the thermistor can be heated to a knowntemperature, and the time required to cool the thermistor to a second,lower temperature will be inversely proportional to blood flow.

According to the present invention, measuring circuits in theabove-described thermal dilution embodiments are automatically activatedonly during estimation of blood flow, and are powered down or offbetween estimates of blood flow. A resulting volumetric blood flow vs.time waveform constructed from the sequence of blood flow estimates isthereby obtained at a reduced power consumption by application of thestrobing technique of the present invention.

The present invention also includes the use of laser Doppler techniquesto estimate blood flow. The blood flow is illuminated with a coherentmonochromatic light source signal. A resulting backscatteredDoppler-shifted light signal is received at an optical detector, anddemodulated such as by mixing with the monochromatic light sourcesignal. Blood flow velocity is estimated from a resulting basebandedDoppler-shifted frequency of the received light signal. According to thepresent invention, measuring circuits, optionally including themonochromatic light source, are automatically activated only duringestimation of the blood flow velocity. These measuring circuits aredeactivated, i.e. powered down or off between estimates of blood flowvelocity. A resulting velocity vs. time waveform constructed from thesequence of blood flow velocity is thereby obtained at a reduced powerconsumption by application of the strobing technique of the presentinvention.

Thus, the present invention provides an strobed blood flow meter, suchas an implantable strobed ultrasonic Doppler blood flow meter, havingreduced average power consumption, which is advantageous for reducingbattery size, improving signal-to-noise ratio, and extending batterylife.

It is to be understood that the above description is intended to beillustrative, and not restrictive. Many other embodiments will beapparent to those of skill in the art upon reviewing the abovedescription. The scope of the invention should, therefore, be determinedwith reference to the appended claims, along with the fill scope ofequivalents to which such claims are entitled.

What is claimed is:
 1. A method of repeatedly estimating fluid flow in aconduit, the method comprising the steps of: (a) illuminating theconduit with ultrasonic energy for an active period of a control signalsufficient to obtain an estimate of fluid flow; (b) receiving anultrasonic energy signal using one or more measurement circuits inresponse to illuminating the conduit with ultrasonic energy; (c)processing the received ultrasonic energy signal using the one or moremeasurement circuits to obtain a fluid flow estimate; (d) interruptingstep (a) for at least a portion of an idle period of the control signal;and (e) reducing power to at least a portion of the one or moremeasurement circuits during the portion of the idle period.
 2. Themethod of claim 1, further comprising repeating steps (a)-(d) over aperiod of time.
 3. The method of claim 2, wherein repeating steps(a)-(d) includes repeating steps (a)-(d) at a strobing frequency greaterthan approximately 50 Hz.
 4. The method of claim 1, wherein the activeperiod in step (a) is longer than a stabilization time.
 5. A method ofrepeatedly estimating fluid flow in a conduit, the method comprising thesteps of: (a) powering up electronic circuits to receive and process asignal representative of fluid flow in the conduit to produce a fluidflow estimate during an active period of a control signal; (b)illuminating the conduit with ultrasonic energy from at least twosources to produce first and second signals during at least a portion ofthe active period; (c) receiving the first and second signals containingtime-shifted frequencies and (d) reducing power to the electroniccircuits during at least a portion of an idle period of the controlsignal.
 6. The method of claim 5, further comprising repeating steps(a)-(d) over a period of time.
 7. The method of claim 5, furthercomprising powering on an amplifier during step (a).
 8. The method ofclaim 5, wherein step (a) comprises powering on a receiver.
 9. Themethod of claim 5, wherein a strobing frequency, corresponding to theinverse of a sum of the active and idle periods, is greater thanapproximately 50 Hz.
 10. The method of claim 5, wherein step (a)comprises powering on a processing circuit.